Flexible stent having protruding hinges

ABSTRACT

The present invention relates to tissue-supporting medical devices and drug delivery systems, and more particularly to tubular flexible stents that are implanted within a body lumen of a living animal or human to support the organ, maintain patency and/or deliver drugs or agents. The tubular flexible stent has a cylindrical shape defining a longitudinal axis and includes a helical section having of a plurality of longitudinally oriented strut members and a plurality of circumferentially oriented hinge members connecting circumferentially adjacent strut members to form a band. The band is wrapped about the longitudinal axis in a substantially helical manner to form a plurality of helical windings. At least one connector member extends between adjacent windings.

CROSS REFERENCE TO RELATED APPLICATION

This application claims the benefit of U.S. Provisional Application, Ser. No. 61/370,011 filed Aug. 2, 2010, which is incorporated by reference herein.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates to tissue-supporting medical devices and drug delivery systems, and more particularly to expandable devices that are implanted within a body lumen of a living animal or human to support the organ, maintain patency and/or deliver drugs or agents.

2. Summary of the Related Art

In the past, permanent or biodegradable devices have been developed for implantation within a body passageway to maintain patency of the passageway and/or locally deliver drug or agent. These devices are typically introduced percutaneously, and transported transluminally until positioned at a desired location. These devices are then expanded either mechanically, such as by the expansion of a mandrel or balloon positioned inside the device, or expand themselves by releasing stored energy upon actuation within the body. Once expanded within the lumen, these devices, typically referred to as stents, become encapsulated within the body tissue and remain a permanent implant.

Known stent designs include monofilament wire coil stents (U.S. Pat. No. 4,969,458); welded metal cages (U.S. Pat. Nos. 4,733,665 and 4,776,337); and, most prominently, thin-walled metal cylinders with axial slots formed around the circumference (U.S. Pat. Nos. 4,733,665, 4,739,762, and 4,776,337). Known construction materials for use in stents include polymers, organic fabrics and biocompatible metals, such as, stainless steel, gold, silver, tantalum, titanium, cobalt chromium and shape memory alloys such as Nitinol.

U.S. Pat. Nos. 4,733,665, 4,739,762, and 4,776,337 disclose expandable and deformable interluminal vascular grafts in the form of thin-walled tubular members with axial slots allowing the members to be expanded radially outwardly into contact with a body passageway. After insertion, the tubular members are mechanically expanded beyond their elastic limit and thus permanently fixed within the body. The force required to expand these tubular stents is proportional to the thickness of the wall material in a radial direction. To keep expansion forces within acceptable levels for use within the body (e.g., 5-10 atm), these designs must use very thin-walled materials (e.g., stainless steel tubing with 0.0025 inch thick walls). However, materials this thin are not visible on conventional fluoroscopic and x-ray equipment and it is therefore difficult to place the stents accurately or to find and retrieve stents that subsequently become dislodged and lost in the circulatory system.

Further, many of these thin-walled tubular stent designs employ networks of long, slender struts whose width in a circumferential direction is two or more times greater than their thickness in a radial direction. When expanded, these struts are frequently unstable, that is, they display a tendency to buckle, with individual struts twisting out of plane. Excessive protrusion of these twisted struts into the bloodstream has been observed to increase turbulence, and thus encourage thrombosis. Additional procedures have often been required to attempt to correct this problem of buckled struts. For example, after initial stent implantation is determined to have caused buckling of struts, a second, high-pressure balloon (e.g., 12 to 18 atm) would be used to attempt to drive the twisted struts further into the lumen wall. These secondary procedures can be dangerous to the patient due to the risk of collateral damage to the lumen wall.

In addition, many of the known stents display a large elastic recovery, known in the field as “recoil,” after expansion inside a lumen. Large recoil necessitates over-expansion of the stent during implantation to achieve the desired final diameter. Over-expansion is potentially destructive to the lumen tissue. Known stents of the type described above experience recoil of up to about 6 to 12% from maximum expansion.

Large recoil also makes it very difficult to securely crimp most known stents onto delivery catheter balloons. As a result, slippage of stents on balloons during interlumenal transportation, final positioning, and implantation has been an ongoing problem. Many ancillary stent securing devices and techniques have been advanced to attempt to compensate for this basic design problem. Some of the stent securing devices include collars and sleeves used to secure the stent onto the balloon.

Another problem with known stent designs is non-uniformity in the geometry of the expanded stent. Non-uniform expansion can lead to non-uniform coverage of the lumen wall creating gaps in coverage and inadequate lumen support. Further, over expansion in some regions or cells of the stent can lead to excessive material strain and even failure of stent features. This problem is potentially worse in low expansion force stents having smaller feature widths and thicknesses in which manufacturing variations become proportionately more significant. In addition, a typical delivery catheter for use in expanding a stent includes a balloon folded into a compact shape for catheter insertion. The balloon is expanded by fluid pressure to unfold the balloon and deploy the stent. This process of unfolding the balloon causes uneven stresses to be applied to the stent during expansion of the balloon due to the folds causing the problem non-uniform stent expansion.

It is desirable to provide flexibility in stents to facilitate introduction of the stent into vessels that are difficult to reach. Often, however, characteristics of the stent that provide longitudinal flexibility, which is desirable when introducing the stent into the vessel, can be disadvantageous in terms of keeping the stent in an expanded condition. For example, stents formed from interconnected rings with closed cell structures or generally diamond-shaped cells are typically less flexible than stents formed from one or more helices, but are usually more uniformly and consistently expandable than helical stents. It is desirable to provide a stent with substantial flexibility that is adapted to be expanded in a uniform and consistent fashion.

In WO 03/015664, which is incorporated by reference, a stent having interconnected struts with openings for drug delivery is disclosed. However, elements for bridging the struts are generally thinner and spaced further apart than the struts. Thus, for such drug-eluting stents, the bridging element can provide an area of reduced or less consistent drug delivery. It is desirable to provide a drug-eluting stent in which areas of reduced or less consistent drug delivery can be reduced.

SUMMARY OF THE INVENTION

The present invention relates to tissue-supporting medical devices and drug delivery systems, and more particularly to expandable, devices that are implanted within a body lumen of a living animal or human to support the organ, maintain patency and/or deliver drugs or agents.

In one embodiment of the invention the flexible stent has proximal and distal end portions and a cylindrical shape, with luminal and abluminal surfaces and a thickness there between. The cylindrical shape defines a longitudinal axis. The flexible stent comprises a helical section having of a plurality of longitudinally oriented strut members and a plurality of circumferentially oriented hinge members connecting circumferentially adjacent strut members to form a band. The band is wrapped about the longitudinal axis in a substantially helical manner to form a plurality of helical windings. Each strut member has a substantially rectangular shape with opposing longitudinally oriented long sides and opposing circumferentially oriented short sides. Each hinge member is connected to the strut members along the short side of each strut member. At least one connector member extends between longitudinally adjacent helical windings of the band and is attached on each end to the short side of a strut member. The connector member not attached to the hinge members.

In another embodiment of the invention the tubular flexible stent has a cylindrical shape with proximal and distal end portions and defining a longitudinal axis. The flexible stent comprises a helical section having of a plurality of longitudinally oriented strut members and a plurality of circumferentially oriented hinge members connecting circumferentially adjacent strut members to form a band. The band is wrapped about the longitudinal axis in a substantially helical manner to form a plurality of helical windings. The helical section comprises a proximal transition zone, a distal transition zone, and a central zone there between, each having a pitch and an incident angle, wherein the pitch and incident angle of the proximal and distal transition zones are different than the central zone.

In still another embodiment of the present invention, the tubular flexible stent has a cylindrical shape with proximal and distal end portions and defining a longitudinal axis. The flexible stent comprises a helical section having of a plurality of longitudinally oriented strut members and a plurality of circumferentially oriented hinge members connecting circumferentially adjacent strut members to form a band. The band is wrapped about the longitudinal axis in a substantially helical manner to form a plurality of helical windings. The helical section further comprises strings formed from groups of contiguous strut members and hinge members organized to form a string pattern, wherein contiguous strings along the band have different string patterns.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is a perspective view of a flexible stent in the expanded (deployed) state according to one embodiment of the present invention.

FIG. 1B is a perspective view of a flexible stent in the crimped state according to one embodiment of the present invention.

FIG. 1C is a perspective view of a flexible stent in the “as cut” (manufactured) state according to one embodiment of the present invention.

FIG. 2 is plan view of a flexible stent according to one embodiment of the present invention.

FIG. 3 is an exploded plan view of the flexible stent of FIG. 2.

FIG. 4A is a close-up plan view of a strut from a flexible stent according to one embodiment of the present invention.

FIG. 4B is a close-up plan view of a strut from a flexible stent according to one embodiment of the present invention.

FIG. 4C is a close-up plan view of a strut from a flexible stent according to one embodiment of the present invention.

FIG. 4D is a close-up plan view of an organically optimized strut from a flexible stent according to one embodiment of the present invention.

FIG. 5A is a close-up plan view of a ductile hinge from a flexible stent according to one embodiment of the present invention.

FIG. 5B is a close-up plan view of a ductile hinge from a flexible stent according to one embodiment of the present invention.

FIG. 5C is a close-up plan view of a ductile hinge from a flexible stent according to one embodiment of the present invention.

FIG. 5D is a close-up plan view of a ductile hinge from a flexible stent according to one embodiment of the present invention.

FIG. 5E is a close-up plan view of a ductile hinge from a flexible stent according to one embodiment of the present invention.

FIG. 6A is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6B is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6C is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6D is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6E is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6F is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6G is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6H is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6I is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6J is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6K is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6L is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 6M is a close-up plan view of a circular hinge region from a flexible stent according to one embodiment of the present invention.

FIG. 7 is a close-up plan view of an index hinge from a flexible stent according to one embodiment of the present invention.

FIG. 8 is a close-up plan view of the central zone depicted in FIG. 3 to illustrate the incident angle of the helical band (wrap).

FIG. 9A is a close-up plan view of a connector strut string that is part of the repeating pattern that forms the central zone of the flexible stent illustrated in FIG. 2 according to one embodiment of the present invention.

FIG. 9B is a close-up plan view of a free strut string that is part of the repeating pattern that forms the central zone of the flexible stent illustrated in FIG. 2 according to one embodiment of the present invention.

FIG. 10 is plan view of a flexible stent according to one embodiment of the present invention.

FIG. 11 is an exploded plan view of the flexible stent of FIG. 10.

FIG. 12 is plan view of a flexible stent according to one embodiment of the present invention.

FIG. 13 is an exploded plan view of the flexible stent of FIG. 12.

FIG. 14 is plan view of a flexible stent according to one embodiment of the present invention.

FIG. 15 is an exploded plan view of the flexible stent of FIG. 14.

FIG. 16 is a close-up plan view of the free strut string and the connector strut string that are part of the repeating pattern that form the central zone of the flexible stent illustrated in FIG. 14 according to one embodiment of the present invention.

FIG. 17 is a close-up plan view of the free strut string and the connector strut string that are part of the repeating pattern that form the central zone of the flexible stent illustrated in FIG. 12 according to one embodiment of the present invention.

FIG. 18 is a close-up plan view of the free strut string and the connector strut string that are part of the repeating pattern that form the central zone of the flexible stent illustrated in FIG. 10 according to one embodiment of the present invention.

FIG. 19 is a plan view of a flexible stent without depots according to one embodiment of the present invention.

DETAILED DESCRIPTION OF THE INVENTION

The stent of the present invention is very flexible and deliverable, while still providing sufficient radial strength to maintain vessel patency. The stent can be formed in any suitable manner, such as by laser cutting a tube made from a suitable material, including cobalt chromium alloys, stainless steel alloys or nickel titanium alloys. Although coronary flexible stents of the present invention are disclosed to illustrate one embodiment of the present invention, one of ordinary skill in the art would understand that the disclosed invention can be equally applied to other locations and lumens in the body, such as, for example, vascular, non-vascular and peripheral vessels, ducts, and the like.

In accordance with one aspect of the present invention, the flexible stent is designed to be crimped down to a reduced diameter and percutaneously delivered through a body lumen to a target site by a delivery catheter. The target site may be, for example, a cardiac artery. Once deployed the flexible stent functions to maintain vessel patency and, if desired, deliver controlled amounts of drug or agent.

Perspective views of a flexible stent 100 in the expanded (deployed), crimped, and “as cut” or manufactured state according to one embodiment of the present invention are illustrated in FIGS. 1A, 1B and 1C respectively. The stent 100 has an “as cut” diameter when first manufactured of D3, as illustrated in FIG. 1C. The stent 100 is crimped down to a first diameter D1, illustrated in FIG. 1B, for insertion into a patient and navigation through the vessels, and a second diameter D2, illustrated in FIG. 1A, for deployment into the target area of a vessel, with the second diameter being greater than the first diameter.

The flexible stent 100 is cylindrical with a tubular configuration of structural elements having luminal and abluminal surfaces, 101, 102 respectively, and thickness (wall thickness) “T” there between. The cylindrical shape of the stent defines a longitudinal axis 103 and has proximal and distal ends portions 104, 105 respectively.

The terms proximal and distal are typically used to connote a direction or position relative to a human body. For example, the proximal end of a bone may be used to reference the end of the bone that is closer to the center of the body. Conversely, the term distal can be used to refer to the end of the bone farthest from the body. In the vasculature, proximal and distal are sometimes used to refer to the flow of blood to the heart, or away from the heart, respectively. Since the flexible stent described in this invention can be used in many different body lumens, including both the arterial and venous system, the use of the terms proximal and distal in this application are used to describe relative position in relation to the direction of delivery. For example, the use of the term distal end portion in the present application describes the end portion of the stent first introduced into the vasculature and farthest from the entry point into the body relative to the delivery path. Conversely, the use of the term proximal end portion is used to describe the back end portion of the stent that is closest to the entry point into the body relative to the delivery path.

FIGS. 2 and 3 are plan views of the stent 100 in a partially expanded condition according to one embodiment of the present invention. As used herein, the term plan view is understood to be a two-dimensional (2-D) view of a stent that has been cut along the longitudinal axis and laid out flat, such that the bottom edge could be wrapped around a cylinder and connected to the top edge.

The stent 100 architecture generally includes ring-like end sections 106, 107 along the proximal and distal ends, 104, 105 respectively, and a helical interior section 108 there between. The helical interior section 108 further includes a central zone 111 and proximal and distal transition zones 109, 110 respectively. The transition zones 109, 110 transition between the central zone 111 and the proximal and distal ring-like end sections 106, 107. FIG. 3 is an exploded plan view of the stent 100 illustrating the different sections and zones.

The stent 100 includes a plurality of longitudinally oriented struts 113 connected by a series of circumferentially oriented ductile hinges 114. Circumferentially adjacent struts 113 are connected at opposite ends by the hinges 114 in a substantially S or Z shaped sinusoidal-like pattern to form a band. Flexible connectors 112 are distributed throughout the stent 100 architecture for structural stability under a variety of loading conditions. The stent design illustrated in FIGS. 1 through 3 have a flexible connector geometry, however, a wide variety of connector geometries are contemplated. See generally FIGS. 6B through 6H.

The region in the stent 100 where the interior helical section 108 is first connected to the ring-like end sections 106, 107 is referred to as an anchor point, and the hinge 114 at that location is referred to as an “anchor hinge”. This “take off” point may vary based on design constraints. Additionally, the incident angle, strut thickness, strut width, hinge width, hinge length, depot position and size, and connection length may vary based on optimization and design constraints.

As used herein the terms longitudinally, circumferentially and radially oriented are known to denote a particular direction relative to the stent 100 and the longitudinal axis 103. A longitudinally oriented member is directed, end to end (along its axis), generally in the direction of the longitudinal axis 103. It is obvious after reviewing the figures that the longitudinal direction of the strut 113 is closer to being parallel to the longitudinal axis when the stent 100 is in the crimped state as illustrated in FIG. 1B, then when the stent 100 is in the expanded, deployed state as illustrated in FIG. 1A. Regardless, in each case, the strut 113 is considered to be longitudinally oriented as the axis of the strut 113 is substantially oriented in the same direction as the longitudinal axis. A circumferentially oriented member, such as hinge 114, is directed substantially along the circumference of the tubular stent 100. Similarly, a radial direction or radially oriented is along a radius that extends generally from the longitudinal axis outward to the circumference of the tubular stent 100 in cross-section.

FIGS. 4A, 4B and 4C illustrate typical struts 113 according to various embodiments of the present invention. Each strut 113 is a substantially rectangular shaped member having longitudinally extending long sides 115 and circumferentially extending short sides 116. Opposing long sides 115 and short sides 116 may be substantially parallel to one another forming a near perfect rectangular as depicted by the strut 113 illustrated in FIG. 4A, or may be canted or angled to form a tapered strut 113 as depicted by the strut 113 illustrated in FIG. 4B. As can be seen in FIGS. 4A and 4B, the hinges 114 attached to the strut 113 along the short sides 116 of the strut, however the width of the strut (length of the short side 116) is greater than the width of the hinge 114 in a preferred embodiment of the invention. As illustrated in FIG. 4B, the flexible connectors 112 connect to the struts 113 along the short sides 116 of the struts 113, but do not connect to the hinges 114.

FIG. 4C represents a unique strut 113 that may be found in some embodiments of the stent 100 design. The strut 113 depicted in FIG. 4C is characterized by two connection points to circular hinges 114 (as hereinafter described) and two connection points to flexible connectors 112. This strut 113 is widest at the proximal and distal ends (at the connection points of the hinges 114 and flexible connectors 112) and tapers to its minimum width near the mid-point in the longitudinal strut 113 length. That is to say the length of the short side 116 of the strut 113 depicted in FIG. 4C is greater than the width near the longitudinal center point of the strut 113.

The struts 113 may have one or more depots 117 for containing at least one agent. The depots 117 may be any form of recess, channel, hole or cavity capable of holding an agent, but are preferably through holes precisionly formed through the stent 100. In a preferred embodiment, the through hole passes through the strut from the luminal to abluminal surface. This preferred configuration may allow an agent or agents to be delivered both in a radially inward and outward direction along the luminal and abluminal sides of the stent 100. In addition, the depots 117 may be filled with a polymer inlay, either alone or containing one or more agents in solution or otherwise. Various depots 117 in the same stent may be filled with the same or different agents, and may have the same or different concentrations of agents. Any individual depot 117 may be filed with one or multiple agents, and the agents may be separated by a barrier layer. The barrier layer may be position in various configurations in the depot 117 as need to separate the agents. In a preferred embodiment, the barrier layer is oriented parallel to the luminal stent surface.

The struts 113 may have symmetrically sized depots 117 as illustrated in FIGS. 4A-4C, or may include organically optimized depots 117 as illustrated in FIGS. 4D. Organically optimized depots 117 are designed to maximize the depot 117 volume for any given strut 113 size, while reducing the stress state of the entire feature through the addition or removal of material critical to maintaining structural integrity upon stent 100 expansion.

As the term is used herein, the agent can be any therapeutic or pharmaceutic agent or drug, including the following: antiproliferative/antimitotic agents including natural products such as vinca alkaloids (i.e. vinblastine, vincristine, and vinorelbine), paclitaxel, epidipodophyllotoxins (i.e. etoposide, teniposide), antibiotics (dactinomycin (actinomycin D) daunorubicin, doxorubicin and idarubicin), anthracyclines, mitoxantrone, bleomycins, plicamycin (mithramycin) and mitomycin, enzymes (L-asparaginase which systemically metabolizes L-asparagine and deprives cells which don't have the capacity to synthesize their own asparagine; antiproliferative/antimitotic alkylating agents such as nitrogen mustards (mechlorethamine, cyclophosphamide and analogs, melphalan, chlorambucil), ethylenimines and methylmelamines (hexamethylmelamine and thiotepa), alkyl sulfonates-busulfan, nitrosoureas (carmustine (BCNU) and analogs, streptozocin), trazenes-dacarbazinine (DTIC); antiproliferative/antimitotic antimetabolites such as folic acid analogs (methotrexate), pyrimidine analogs (fluorouracil, floxuridine, and cytarabine), purine analogs and related inhibitors (mercaptopurine, thioguanine, pentostatin and 2-chlorodeoxyadenosine {cladribine}); platinum coordination complexes (cisplatin, carboplatin), procarbazine, hydroxyurea, mitotane, aminoglutethimide; hormones (i.e.estrogen); Anticoagulants (heparin, synthetic heparin salts and other inhibitors of thrombin); fibrinolytic agents (such as tissue plasminogen activator, streptokinase and urokinase), aspirin, dipyridamole, ticlopidine, clopidogrel, abciximab; antimigratory; antisecretory (breveldin); anti-inflammatory: such as adrenocortical steroids (cortisol, cortisone, fludrocortisone, prednisone, prednisolone, 6α-methylprednisolone, triamcinolone, betamethasone, and dexamethasone), non-steroidal agents (salicylic acid derivatives i.e. aspirin; para-aminophenol derivatives i. e. acetominophen; Indole and indene acetic acids (indomethacin, sulindac, and etodalac), heteroaryl acetic acids (tolmetin, diclofenac, and ketorolac), arylpropionic acids (ibuprofen and derivatives), anthranilic acids (mefenamic acid, and meclofenamic acid), enolic acids (piroxicam, tenoxicam, phenylbutazone, and oxyphenthatrazone), nabumetone, gold compounds (auranofin, aurothioglucose, gold sodium thiomalate); immunosuppressive: (cyclosporine, tacrolimus (FK-506), sirolimus (rapamycin), azathioprine, mycophenolate mofetil); angiogenic: vascular endothelial growth factor (VEGF), fibroblast growth factor (FGF); nitric oxide donors; anti-sense oligo nucleotides and combinations thereof.

One or more agents may be distributed in one or more of the depots 117, along at least a portion of the luminal or abluminal stent 100 surfaces, or any combination of depots and/or stent surfaces. In a preferred embodiment, the agent is distributed in the depots 117 only, such that the exposed agent surface area is limited to the cross-sectional area of the depot opening in the stent 100 surface (luminal, abluminal or both). This design allows for agent delivery from the stent 100 having a surface area upon insertion into the patient that is substantially bare metal. In a preferred embodiment, the exposed bare metal surface area of the stent 100 is between 40 and 95 percent upon insertion of the stent 100 into a patient, and is most preferably approximately 75 percent bare metal upon insertion of the stent 100 into a patient. That is, the surface area of the stent 100 is approximately 25 percent agent and approximately 75 percent bare metal. As the agent is released, the stent 100 becomes a purely bare metal stent.

In a preferred embodiment, the depots 117 are distributed nearly uniformly throughout the strut pattern to provide a consistent agent dosage per unit surface area of the deployed stent 100 independent of the diameter or length of the stent used. The struts 113 may be of varying lengths, incident angle, depot configuration, and widths as needed to meet the product design.

Ductile hinges 114 are used as the connection element between two circumferentially adjacent struts 113. There are two types of ductile hinges 114 found in stent 100. FIGS. 5A and 5B illustrate the two typical ductile hinges found in one embodiment of the present invention. FIG. 5A represents a single “free hinge” 114 a that connects two circumferentially adjacent struts 113. In a preferred embodiment, this free hinge 114 a is “C” shaped and is substantially symmetric about reference line “A” drawn though the apex point on the curved section. FIG. 5B represents a ductile hinge 114 b that connects two circumferentially adjacent struts 113, where one of the struts is further connected to a flexible connector 112. This ductile hinge 114 b is more circular in shape than the “C” shaped free hinge 114 a disclosed in FIG. 5A, and is sometimes referred hereto as a “circular hinge” 14 b. Although free hinges 114 a and connector hinges 114 b are identified separately here, they are sometimes generally both referred to as ductile hinges 114. The regions surrounding the circular hinge 14 b is referred to as a circular hinge region. While the flexible connector 112 and circular ductile hinge 114 b both connect to the same short side 116 of the strut 113 in the circular hinge region, they are not connected to one another.

FIG. 5C is a magnified plan view of another inventive single free hinge according to one embodiment of the present invention. Similar to the hinge depicted in FIG. 5A, hinge 114 c connects two circumferentially adjacent struts 113. In a preferred embodiment, this free hinge 114 c has a crown along the curve between the two connecting struts 113. In a preferred embodiment, the free hinge 114 c is substantially symmetric about reference line “A” drawn though the apex point on the curved section. The crown is formed by two minor arcs extending inward, and one greater arc forming the protrusion extending outward. The crown can also be formed by a protrusion outward while the hinge maintains a continuous interior, i.e. a continuous intrados with a crowned exterior.

While the crown in FIG. 5C is shown protruding outward, the crown may also face inward, in the form of a dimple on hinge 114 d, as illustrated in FIG. 5E. The dimple is formed by one minor arc extending inward, forming the protrusion, and two greater arcs extending out outward. The dimple can also be formed by a protrusion inward while the hinge maintains a continuous exterior, i.e. a continuous extrados with a dimpled interior.

There are several advantages of this design. The crown hinges 114 c, 114 d have an increased hinge path length—the length of the curve between the two connecting struts. This feature increases the surface area where plastic strains can be distributed, thereby reducing peak plastic strains. The increased hinge path length is accomplished by the additional undulations that form the crown. The design may also allow for decreased hinge height while maintaining equivalent stresses and strains when compared to hinges without crowns or dimples.

In addition, the expansion dynamics of a hinge with such a protrusion creates a locking mechanism, much like a leaf spring. Upon expansion, the interior arc element is thrust forward and plastically deformed allowing the hinge pair to lock.

FIG. 5D is a close-up plan view of the ductile hinge 114 c from a flexible stent according to one embodiment of the present invention. The hinge 114 c depicted in the figure has a centerline width, identified by reference line B. The centerline width is the distance between circumferentially adjacent struts 113 connected by the hinge 114 c, measured from the centerline of the hinge end where the hinge 114 c meets the strut 113. The centerline length C of the hinge is depicted as reference curve C in FIG. 5D. The centerline length C is the length of the hinge, measured from end to end along the hinge centerline. The ratio of centerline length to centerline width is approximately 1.875:1

In addition, the hinge incorporates geometry that localizes plastic strain during the crimping procedure and distributes the plastic strains during deployment. The crown feature of the hinge 114 c serves as a “crumple zone” during crimping, leading to localized plastic strains within the crown during crimp loading. This localization of plastic strains during the crimp process results in smaller stent recoil, which ultimately decreases system crossing profile. A simplified 2D model of the crown hinge 114 c indicated a 48% reduction in stent crimp recoil over earlier designs.

During deployment, the crown design also distributes plastic strains during stent deployment loading, leading to overall lower peak plastic strain. The decreased plastic strain allows for increased stent structural integrity both from an acute and long-term fatigue perspective. A 10% reduction in peak plastic strain after deployment was observed during 2D FEA modeling.

The crown hinge design also provides increased radial stiffness in the crimped and expanded configurations, leading to increased securement. In addition the increased stiffness in the expanded configuration will provide resistance to in-vivo radial compression loading. The 2D FEA modeling disclosed a 12% increase in hinge radial stiffness in the crimped configuration.

The crown hinge 114 c utilized a constant width across the hinge length. However, a non-uniform width, such as width tapering, the path length of the hinge may be utilized in an effort to further distribute the plastic strains through the hinge region. The non-uniform width distribution could also be utilized to further increase the hinge stiffness and decrease hinge recoil.

FIG. 6A provides greater detail of the “circular hinge region” 118 that serves as a connection point between two strut pairs on adjacent windings of the helical section 108. This hinge region 118 includes several components, and provides a ductile region in between circumferentially adjacent struts 113 that form a strut pair, while providing the necessary connectivity between longitudinally adjacent strut pairs by the flexible connector 112. When combined, the longitudinally adjacent strut pairs and interconnecting flexible connector 112 create regions known as “quad hinge regions”. These regions are comprised of four struts that are directly or indirectly connected through the circular hinges 114 b and flexible connectors 112. The incident angle, hinge 114 b width, degree of taper, length, and hole pattern are subject to change based on the stents intended design, the location of the feature and stent performance optimization. FIGS. 6B through 6M illustrated various connectors 112 that can be use to connect adjacent strut pairs in the circular hinge region 118.

FIG. 7 illustrates another key stent attribute important during the manufacturing process of the stent 100. The encircled ductile hinge 114 is known as the “index hinge”. This “index hinge” is characterized by longer strut 113 lengths, which causes the ductile hinge or strut 113 head to protrude beyond the plane of the strut 113 heads on the remaining struts within the sinusoidal end ring. For ease of illustration, reference line A has been drawn perpendicular to the longitudinal axis 103 and tangent to the curved surfaces of both the hinges 114 above and below the index hinge. Reference line B has been drawn perpendicular to the longitudinal axis 103 and tangent to the curved surface of the hinge 114 representing the index hinge. The distance between reference lines A and B along the longitudinal axis is the offset provided by the index. This offset serves as a reference point to help determine the orientation of the stent 100. The “index hinge” may occur at any location along the proximal and distal ring-like end sections 106, 107.

Generally speaking, the ductile hinges 114 are deformable elements that are substantially thinner in width than the surrounding struts 113. This allows the ductile hinges 114 to sustain plastic deformation while still remaining flexible in the deformed state. The struts 113 are therefore much stiffer than the ductile hinges 114, and thus do not experience any plastic deformation during stent expansion. The struts 113 essentially rotate as rigid bodies, while the ductile hinges 114 are designed to the bear the plastic strains associated with stent expansion. As a result, the depots 117 in the struts 113 are shielded from undue stress during expansion that may cause damage or dislodgement of the agents and/or polymer inlays. The depots 117 are ideally in a stress-free state throughout the stent deployment process.

In a preferred embodiment of the present invention, the ductile hinges 114 are optimized, through the use of width tapering, such that they offer sufficient radial stiffness to the stent 100 while simultaneously ensuring that peak plastic strains at full expansion do not exceed the strain carrying capability of the material. This width tapering is optimized, for each hinge 114 type, to achieve a smooth and uniform distribution of plastic strains along the length of the ductile hinge 114. By smoothing the strain distribution and thus eliminating strain concentrations in the ductile hinge 114, the width, and thereby stiffness, is maximized. Maximizing the stiffness of the ductile hinge 114 is advantageous in providing radial stiffness and fatigue durability for the stent 100.

In general the width of the tapered ductile hinge 114 gradually increases while approaching the root of the hinge 114, where the hinge 114 meets an abrupt transition into the wider strut 113 (or stiffer structure). This prevents plastic strains from concentrating at the roots of the hinges since the tapered hinge root is stiffer and therefore distributes plastic strain to the central portion of the hinge 114. The central portion of the ductile hinge 114, which encompasses the apex of the curve, generally has a uniform width.

Turning again to FIGS. 2 and 3, the ring-like end sections 106, 107 include a plurality of circumferentially arranged, longitudinally oriented strut members 113 connected at opposite ends by a plurality of circumferentially oriented ductile hinges 114 in a substantially sinusoidal S or Z shaped pattern so as to form the band into an endless ring. In the illustrated embodiment, the end sections 106, 107 are formed from struts 113 of varying length as needed optimize the stent design and provide the necessary geometry for the connection at the anchor point where the interior helical section 108 is first connected to the ring-like end sections 106, 107.

Between the ring-like end sections 106, 107 lies the interior helical section 108 of the stent 100, where the band of sinusoidally arranged struts 113 and hinges 114 follow a helical path. The helical band of the interior section 108 is achieved by arranging the struts 113 in a repeating pattern of alternating short and long lengths. The helical interior section 108 may be further divided into proximal and distal transition zone 109, 110 respectively, and a central zone 111.

The central zone 111 comprises strings (collections of elements) formed from groups of contiguous strut members 113 and hinge members 114 organized to form a string pattern. In one embodiment of the invention, contiguous strings have different string patterns and repeating strings are geometrically symmetric to form a repeating central pattern. In a preferred embodiment of the invention, the repeating central pattern consists of two different repeating strings. The central zone 111 therefore has a constant pitch and incident angle.

As used herein the term pitch is understood to mean the number of sinusoidal turns over a given area. This is similar nomenclature to the diametral pitch of a gear. The greater the pitch, the greater the number of sinusoidal turns, i.e. the greater number of struts 113 and ductile hinges 114, will be found per wrap as the sinusoidal band winds about the longitudinal axis 103. This creates a very dense pattern of struts 113 and hinges 114. Conversely, the smaller the pitch, the smaller number of sinusoidal turns, and thus the smaller number of struts 113 and hinges 114 will be found per wrap as the sinusoidal band winds about the longitudinal axis 103. The term incident angle refers specifically to the helical winding section of the stent 100 and is understood to mean the angle at which the sinusoidal band makes (wraps) with the longitudinal axis.

FIG. 8 is a close up 2 dimensional view of the central zone 111 depicted in FIG. 3. A first reference line “A” has been drawn parallel to the longitudinal axis 103. A second reference line “B” has been drawn to represent the direction of the sinusoidal band. The incident angle (α) is the angle between reference line A and reference line B.

FIGS. 9A and 9B illustrate the two strut strings that are part of the repeating pattern that form the central zone 111 of the stent 100 according to one embodiment of the present invention. Referring to FIG. 3, 8, 9A and 9B, the central zone 111 starts at the proximal end of the distal transition zone 110 with a free strut string 119 illustrated in FIG. 9B. The illustrated free strut string 119 includes a long three depot strut 113 connected on each end to a short two depot strut 113 by a free hinge 114 a. The free strut string 119 is attached on its proximal end to the distal end of a connector strut string 120. The connector strut string 120 includes a connector hinge 114 b at its proximal and distal ends, and an alternating arrangement of three long (three depot) struts 113 and two short (two depot) struts 113 connected by free hinges 114 a. This pattern of alternating free strut strings 119 and connector strut strings 120 continue until the central zone 111 meets the proximal transition zone 109. The embodiment illustrated in FIG. 3 has a central zone that includes five free strut strings 119 and four connector strut strings 120. The length of the stent 100 can be changed by adding or shortening the central zone 111, i.e. by adding or removing free strut strings 119 or connector strut strings 120 as necessary to maintain the repeating pattern, while maintaining the proximal and distal transition zones 109, 110, and proximal and distal ring-like end section 106, 107 as disclosed.

The proximal and distal transition zones 109, 110 are sections of variable pitch, and in which there is no repeatability or symmetry. The proximal and distal transition zones 109, 110 are constructed so as to afford a gradual decrease in pitch in transitioning between the central zone 111 and the proximal and distal ring-like end sections 105, 107. The proximal and distal transition zones 109, 110 are connected to the proximal and distal ring-like end section 106, 107, respectively, by a connecting geometry called an anchor hinge.

The stent 100 designs depicted in the aforementioned figures are known as an open cell design, meaning that connectors between longitudinally adjacent windings of sinusoidal elements occur only intermittently through the structure rather than spanning every longitudinally adjacent hinge 114 or strut 113. A design in which every longitudinally adjacent hinge or strut is connected is known as a closed cell design. An open-celled architecture is generally more flexible than a closed-cell architecture.

As previously described, the general architecture of the stent 100 includes a helical interior section 108 with ring-like end sections 106, 107 at each end, and connectors 112 distributed through the architecture for structural stability under a variety of loading conditions. The helical interior section 108 may be further separated into a central zone 111 having a constant pitch and incident angle, and proximal and distal transition zones 109, 110 respectively. This general architecture remains the same for various stents of different sizes; however, the geometry and pattern of the elements (struts, hinges and flex connectors) may change as need to adapt to various desired stent diameters.

FIGS. 10 through 15 illustrate various embodiments of the stent designs for different diametrically size stents. FIGS. 10, 12 and 14 are two-dimensional plan views, similar to FIG. 2, illustrating stents 200, 300, 400, respectively, of different sizes and patterns. FIGS. 11, 13 and 15 are exploded plan views, similar to FIG. 3, of the stents 200, 300, 400, respectively, illustrating the different sections and zones. For ease of illustration, like reference numerals have been assigned to like elements of the stent 100, and it is understood that the description of elements related to stent 100 applies equally to like elements in stents 200, 300 and 400.

Each stent pattern design is customized to target optimal results based on the treatment of the stent's intended target vessel. FIGS. 10 and 11 represents one embodiment of a stent 200 intended for extra small diameter target vessel lesions. The extra small diameter stent family has been optimized for very small vessel diameters via several design features, and is meant to be fabricated from a smaller diameter tubing material.

The current embodiment for an extra small stent includes sinusoidal proximal and distal ring-like end sections 206, 207 comprised of ten struts 213 in each ring-like end sections 206, 207. Between the ring-like end sections 206, 207 lies the interior helical section 208 of the stent 200, where the sinusoidal arrangement of struts 213 and hinges 214 follow a helical path. The helical path of the interior section 208 is achieved by arranging the struts 213 in a repeating pattern of alternating short and long lengths to form a band. There are nine struts 213 per winding in each the interior bands. The fewer number of struts allows for increased stent performance while maintaining critical processing parameters. The helical interior section 208 may be further divided into proximal and distal transition zones 209, 210 respectively and a central zone 211 as illustrated in FIG. 11.

The central zone 211 consists of repeating strut strings, or collections of struts, which are geometrically symmetric to form a repeating pattern in the band. The central zone 211 therefore has a constant pitch and incident angle. The repeating interior pattern is comprised of two 3-strut patterns that alternate to form the 9-strut repeating interior pattern.

FIG. 18 illustrates the two strut strings 219, 220 that are part of the repeating pattern from the central zone 211 of the stent 200 according to one embodiment of the present invention. Referring to FIGS. 10, 11 and 18, the central zone 211 starts at the distal end of the proximal transition zone 209 with a free strut string 219 illustrated in FIG. 18. The illustrated free strut string 219 includes a long (four depot) strut 213 connected on each end to a short (two depot) strut 213 by a free hinge 214 a. The free strut string 219 is attached on its distal end to the proximal end of a connector strut string 220. The connector strut string 220 includes a connector hinge 214 b at its proximal and distal ends, and an alternating arrangement of two long (four depot) struts 213 and one short (two depot) strut 213 connected by free hinges 214 a. This pattern of alternating free strut strings 219 and connector strut strings 220 continue until the central zone 211 meets the distal transition zone 210. The embodiment illustrated in FIGS. 10 and 11 have a central zone that includes six free strut strings 219 and six connector strut strings 220.

The current embodiment for a medium sized stent includes sinusoidal proximal and distal ring-like end sections 306, 307 comprised of twelve strut 313 end rings. Between the ring-like end sections 306, 307 lies the interior helical section 308 of the stent 300, where the sinusoidal arrangement of struts 313 and hinges 314 in the band follow a helical path. The helical path of the interior section 308 is achieved by arranging the struts 313 in a repeating pattern of alternating short and long lengths to form the band. There are thirteen struts 313 per band winding in the interior helical section 308. The increased number of struts allows for increased stent performance while maintaining critical processing parameters. The helical interior section 308 may be further divided into proximal and distal transition zones 309, 310 respectively and a central zone 311 as illustrated in FIG. 13.

The central zone 311 consists of repeating strut strings, or collections of struts, which are geometrically symmetric to form a repeating pattern. The central zone 311 therefore has a constant pitch and incident angle. The repeating interior pattern is comprised of one 3-strut pattern and one 5-strut pattern that alternate to form the 13-strut repeating interior pattern.

FIG. 17 illustrates the two strut strings 319, 320 that are part of the repeating pattern forming the central zone 311 of the stent 300 according to one embodiment of the present invention. Referring to FIGS. 12, 13 and 17, the central zone 311 starts at the distal end of the proximal transition zone with a connector strut string 320 illustrated in FIG. 17. The illustrated connector strut string 320 includes a connector hinge 314 b at its proximal and distal ends, and an arrangement of three long (three depot) struts 313 connected by free hinges 314 a. The free strut string 319 is attached on its proximal end to the distal end of the connector strut string 320. The illustrated free strut string 319 includes a series of three long (three depot) struts 313 interconnected by a free hinge 314 a. The three, three depot struts 313 are connected on each end to a short two depot strut 313 by free hinges 314 a. The pattern of alternating connector strut strings 320 and free strut strings 319 continue until the central zone 311 meets the distal transition zone 310. The embodiment illustrated in FIGS. 12 and 13 has a central zone that includes three connector strut strings 320 and two free strut strings 319. The length of the stent 300 can be changed by adding or shortening the central zone 311, i.e. by adding or removing connector strut strings 320 or free strut strings 319 as necessary to maintain the repeating pattern, while maintaining the proximal and distal transition zones 309, 310 and proximal and distal ring-like end section 306, 307 as disclosed.

FIGS. 14 and 15 represents one embodiment of a stent 400 intended for a large diameter target vessel lesions. The large diameter stent family has been optimized for larger vessels via several design features. Like previous designs, the current embodiment contains sinusoidal proximal and distal ring-like end sections 406, 407 comprised of twelve struts 413. The struts 413 in said end sections 406, 407 are of varying length; however, on the whole they are longer in the large diameter stent design than the typical strut of an equivalent smaller nominal stent design. The end sections 406, 407 are connected via several points to the proximal and distal transition zones 409, 410 as illustrated in FIG. 15.

FIG. 16 illustrates the two strut strings that are part of the repeating pattern from the central zone 411 of the stent 400 according to one embodiment of the present invention. Referring to FIGS. 14, 15 and 16, the central zone 411 starts at the proximal end of the distal transition zone 410 with a free strut string 419 illustrated in FIG. 16. The illustrated free strut string 419 includes an alternating arrangement of short (three depot) struts 413 and long (four depot) struts (413) interconnected on each end by a free hinge 414 a. The free strut string 419 is attached on its proximal end to the distal end of a connector strut string 420. The connector strut string 420 is three struts 413 long, and includes a connector hinge 414 b at its proximal and distal ends. The three struts in the connector string 420 include an alternating arrangement of long (four depot) struts 413 and a short (three depot) strut 413 connected by free hinges 414 a. This pattern of alternating free strut strings 419 and connector strut strings 420 continue until the central zone 411 meets the proximal transition zone 409. The embodiment illustrated in FIG. 15 has a central zone that includes three free strut strings 419 and two connector strut strings 420.

The present invention also contemplates the use of solid struts in similar strut/hinge orientations as those disclosed in FIGS. 2, 10, 12, and 14. FIG. 19 illustrates a stent 500 having similar design architecture without depots along the struts 513. Stent 500 can be used as a bare metal stent or can be partially or completely coated with an agent and/or appropriate carrier as is known in the art. 

1. A tubular flexible stent having proximal and distal end portions and a cylindrical shape, with luminal and abluminal surfaces and a thickness there between, the cylindrical shape defining a longitudinal axis, the tubular flexible stent comprising: a helical section having of a plurality of longitudinally oriented strut members and a plurality of circumferentially oriented hinge members connecting circumferentially adjacent strut members to form a band, the band being wrapped about the longitudinal axis in a substantially helical manner to form a plurality of helical windings, each strut member having a substantially rectangular shape with opposing longitudinally oriented long sides and opposing circumferentially oriented short sides, each hinge member having a curvilinear shape with an inside curve and an outside curve, and having a protruding crown along at least one of the inside curve or the outside curve .
 2. The flexible stent of claim 1 wherein the crown protrudes outward from the outside curve.
 3. The flexible stent of claim 1 wherein the outwardly protruding crown is formed by two minor arcs extending inward on opposite ends of a greater arc along the outside curve.
 4. The flexible stent of claim 2 wherein the inside curve of the hinge maintains a continuous smooth intrados.
 5. The flexible stent of claim 1 wherein the crown protrudes inward from the inside curve.
 6. The flexible stent of claim 1 wherein the inwardly protruding crown is formed by two greater arcs extending outward on opposite ends of a minor arc along the inside curve.
 7. The flexible stent of claim 5 wherein the outside curve of the hinge maintains a continuous smooth extrados.
 8. The flexible stent of claim 1 wherein at least one hinge member has a protruding crown providing a hinge centerline length that is greater than 1.875 times the hinge centerline width.
 9. The flexible stent of claim 1 wherein at least one hinge has a non-uniform width from a first region adjacent the crown to a second region adjacent the strut member.
 10. The flexible stent of claim 9 wherein the at least one hinge tapers from a first width adjacent the crown to a second width adjacent the strut member. 